Osteoimplant and method for making same

ABSTRACT

A method of manufacturing an osteoinductive osteoimplant is provided which comprises the steps of: demineralizing part or all of at least one surface of a monolithic section of cortical bone to a depth of at least about 100 microns; and, configuring the monolithic section of cortical bone to provide an osteoimplant possessing an outer surface possessing at least one demineralized zone and a non-demineralized zone. An implant produced according to the above method demonstrates improved osteoinduction without producing any clinically significant reduction of strength in critical regions of the osteoimplant.

CROSS-REFERENCE TO RELATED APPLICATIONS

This is a continuation of co-pending application Ser. No. PCT/US01/15599filed in English on May 14, 2001 and which claims benefit under 35U.S.C. §119(e) of Provisional Appln. Ser. Nos. 60/204,069 and 60/221,056respectively filed May 12, 2000 and Jul. 27, 2000, and acontinuation-in-part of U.S. application. Ser. No. 09/328,242 filed Jun.8, 1999 and now U.S. Pat. No. 6,277,149 issued Aug. 21, 2001, the entirecontents of all of which are incorporated herein by this reference.

BACKGROUND OF THE INVENTION

1. Field of the Invention

The present disclosure is directed to a method for preparing a partiallydemineralized bone graft. More specifically, this invention relates to aload-bearing osteogenic osteoimplant fabricated from a monolithicsection of cortical bone and to a method for making the osteoimplant aswell as a method of using same.

2. Description of the Related Art

Shaped or cut bone segments have been used extensively to solve variousmedical problems in human and animal orthopedic surgical practice andtheir application has also extended to the field of cosmetic andreconstructive surgery, dental reconstructive surgery, and other medicalfields involving surgery of hard tissues. The use of autograft bone(where the patient provides the source), allograft bone (where anotherindividual of the same species provides the source), xenograft bone(where another individual of a different species provides the source) ortransgenic bone (where a transgenic species provides the source) is wellknown in both human and veterinary medicine. In particular, transplantedbone is known to provide support, promote healing, fill bony cavities,separate bony elements (such as vertebral bodies), promote fusion (wherebones are induced to grow together into a single, solid mass), orstabilize the sites of fractures. More recently, processed bone has beendeveloped into shapes for use in new surgical applications, or as newmaterials for implants that were historically made of non-biologicallyderived materials.

Osteoimplants come in a variety of shapes and sizes including cutcross-sections, cylindrical dowels, cortical rings, elongated struts,wedges, blocks, screws, pins, etc., as well as assembled implants madeof two or more bone pieces such as, for example, described in U.S. Pat.No. 5,899,939 to Boyce et al., U.S. Pat. No. 6,025,538 to Yaccarino,III, U.S. Pat. No. 6,123,731 to Boyce et al., and U.S. Pat. No.6,200,347 B1 to Anderson et al., the contents of each being incorporatedherein by reference. Osteoimplants are used in a variety of differentsurgical procedures including bone fracture repair, spinal fusionprocedures, tendon repair, cosmetic surgery, etc. Typically,osteoimplants will include engagement structure formed integrallytherein for detachable engagement of an implant insertion tool tofacilitate insertion of the osteoimplant into an implant site. Suchengagement structure may include a threaded bore, multiple bore holes, ahexagonal recess, an irregular shape recess, etc. For accurate insertionof the osteoimplant at the surgical site, it is important that closetolerances be maintained between the implant insertion tool and theengagement structure of the osteoimplant.

Bone grafting applications are differentiated by the requirements of theskeletal site. Certain applications require a “structural graft” inwhich one role of the graft is to provide mechanical or structuralsupport to the site. Such grafts contain a substantial portion ofmineralized bone tissue to provide the strength needed for load-bearing.Examples of applications requiring a “structural graft” includeintercalary grafts, spinal fusion, joint plateaus, joint fusions, largebone reconstructions, etc. Other applications require an “osteogenicgraft” in which one role of the graft is to enhance or accelerate thegrowth of new bone tissue at the site. Such grafts contain a substantialportion of demineralized bone tissue to improve the osteoinductivityneeded for growth of new bone tissue. Examples of applications requiring“osteogenic graft” include deficit filling, spinal fusions, jointfusions, etc. Grafts may also have other beneficial biologicalproperties, such as, for example, serving as delivery vehicles forbioactive substances. Bioactive substances include physiologically orpharmacologically active substances that act locally or systemically inthe host.

When mineralized bone is used in osteoimplants, it is primarily becauseof its inherent strength, i.e., its load-bearing ability at therecipient site. The biomechanical properties of osteoimplants uponimplantation are determined by many factors, including the specific sitefrom which the bone used to make the osteoimplant is taken; the age,sex, and physical characteristics of the donor; and the method chosen toprepare, preserve, and store the bone prior to implantation, as well asthe type of loading to which the graft is subjected.

Structural osteoimplants are conventionally made by processing, and thenmachining or otherwise shaping cortical bones collected for transplantpurposes. Cortical bone can be configured into a wide variety ofconfigurations depending on the particular application for thestructural osteoimplant. Structural osteoimplants are often providedwith intricate geometries, e.g., series of steps; concave or convexsurfaces; tapered surfaces; flat surfaces; surfaces for engagingcorresponding surfaces of adjacent bone, tools, or implants, hex shapedrecesses, threaded holes; serrations, etc.

One problem associated with many structural osteoimplants is that theyare never fully incorporated by remodeling and replacement with hosttissue. This is due, in part, to the difficulty with which the host'sblood supply may penetrate cortical bone. Moreover, non-demineralizedbone is not osteoinductive. Since repair is a cellular-mediated process,dead (non-cellular, allograft or xenograft) bone is unable to repairitself. When the graft is penetrated by host cells and host tissue isformed, the graft is then capable of repair. It has been observed thatfatigue damage is usually the result of a buildup of unrepaired damagein the tissue. Therefore, to the extent that the implant is incorporatedand replaced by living host bone tissue, the body can then recognize andrepair damage, thus eliminating failure by fatigue. In applicationswhere the mechanical load-bearing requirements of the osteoimplant arechallenging, e.g., intervertebral spinal implants for spinal fusion,lack of substantially complete replacement by host bone tissue maycompromise the osteoimplant by subjecting it to repeated loading andcumulative unrepaired damage in the tissue (mechanical fatigue) withinthe implant material. Thus, it is highly desirable that the osteoimplanthas the capacity to support load initially and be capable of graduallytransferring this load to the host bone tissue as it remodels theimplant.

As stated above, a known technique for promoting the process ofincorporation of osteoimplants is demineralization. The process ofdemineralizing bone grafts is well known. In this regard see,Lewandrowski et al., J. Biomed Materials Res, 31, pp. 365–372 (1996);Lewandrowski et al., Calcified Tiss. Int., 61, pp. 294–297 (1997);Lewandrowski et al., J. Ortho. Res., 15, pp. 748–756 (1997), thecontents of each of which is incorporated herein by reference. However,the prior art has not addressed the need to provide a demineralizedosteoimplant with sufficiently mineralized regions for engagement ofinsertion instrumentation.

Demineralizing bone, using for example, a controlled acid treatment,increases the osteoinductive characteristics of the osteoimplant.Demineralization also provides the osteoimplant with a degree offlexibility. However, removal of the mineral components of bonesignificantly reduces mechanical strength of bone tissue. See,Lewandrowski et al., Clinical Ortho. Rel. Res., 317, pp. 254–262 (1995).Thus, demineralization sacrifices some of the load-bearing capacity ofmineralized cortical bone and as such is not suitable for allosteoimplant designs. Another disadvantage to the demineralizationprocess is the likelihood of creating dimensional changes in theosteoimplant. Demineralization of the bone will ordinarily result inbone of slightly smaller dimensions. Such changes of dimension can makeit difficult for a configured piece to mechanically engage with surgicalinstruments, other implants, or the prepared surgical site.

Accordingly, a need exists for an improved process for demineralizing anosteoimplant to achieve an improved biologic response to the implantwhile maintaining a mineralized portion of the osteoimplant that canendure mechanical forces and/or maintain close tolerances with insertioninstrumentation and/or the implant site. Complete mineralization may beespecially important for portions of an osteoimplant experiencing thegreatest mechanical loads such as engagement structure of theosteoimplant. In certain embodiments, these areas are masked from thedemineralization process. In other embodiments, a demineralized portionof the osteoimplant is removed by, for example, configuring, to exposethe mineralized portion beneath the demineralized surface region.

It would be advantageous if a surface demineralized load-bearingosteoinductive osteoimplant could be achieved efficiently and accuratelyby a simple process. Use of such an osteoimplant in a load-bearingprocedure such as, for example, joint plateau revisions, joint fusions,spinal fusions, long bone reconstructions, etc. would provide afavorable outcome for the recipient of the implant.

BRIEF SUMMARY OF THE INVENTION

A method of manufacturing a surface demineralized osteoinductiveosteoimplant is provided which comprises the steps of: demineralizingpart or all of at least one surface of a monolithic section of bone to adepth of at least about 100 microns; and, configuring the monolithicsection of bone to provide an osteoimplant possessing an outer surfacepossessing at least one demineralized zone and at least onenon-demineralized zone.

An implant produced according to the above method demonstrates improvedosteoinduction without producing any undesirable clinically significantreduction of strength. Further embodiments of the above method providefor methods of configuring, for example, cutting, machining, or shapingthe osteoimplant, either before and/or after demineralization to providean osteoimplant having desirable characteristics depending upon theintended application. Yet even further embodiments of the method hereinprovided for selective masking of regions of the bone prior todemineralization to prevent any undesirable changes in certaindimensions of the bone as well as to provide the ability to tailor theosteoinductive/load-bearing characteristics of specific portions of theosteoimplant depending upon the intended use of the osteoimplant. Animplant prepared in accordance with this embodiment also provides amineralized zone and a demineralized zone, however, a mineralized zonewill be presented on the surface of the implant as well as in the innercore of the implant.

Also provided is a surface demineralized osteoinductive osteoimplantmade of a monolithic section of bone that has at least one outer surfacepossessing at least one demineralized zone and a non-demineralized core,wherein the demineralized zone of the outer surface of the bone is atleast about 100 microns thick.

Also provided is a vertebral interbody fusion device made of amonolithic section of bone configured to span an intervertebral spacebetween adjacent vertebrae or an intervertebral space spanningnon-adjacent vertebrae, in which the bodies of the intervening vertebraeare replaced in their supportive function by the graft. The bone has atleast one outer surface with at least one demineralized zone forcontacting the adjacent vertebra. The bone also has a non-demineralizedcore to provide for load-bearing. The demineralized zone of the outersurface of the bone is at least about 100 microns thick.

Also provided is a method of promoting joint fusion in an animal in needthereof. The method involves implanting in the animal a load-bearingosteoinductive osteoimplant made of bone having an outer surfacepossessing at least one demineralized zone and a non-demineralized zone.The demineralized zone of the outer surface of the bone is at leastabout 100 microns thick.

Also provided is a method of treating a bone defect in an animal in needthereof. The method consists of applying an osteoinductive osteoimplantmade of bone having an outer surface possessing at least onedemineralized zone and a non-demineralized zone. The demineralized zoneof the outer surface of the bone is at least about 100 microns thick.The osteoimplant is applied to the defect site such that the surface ofthe osteoimplant conforms to the surface of the bone defect site.

Also provided is a osteoimplant implantation kit containing anosteoimplant and a delivery tool useful in performing the placement ofthe osteoimplant during a surgical procedure. The osteoimplant may beprovided in a presterillzed, prepackaged form held by the delivery tool,which can be used without repositioning the osteoimplant in the tool.The implantation tool carries the osteoimplant so as to avoid damage tothe osteoimplant prior to and during surgical implantation. The toolalso permits the surgeon to securely hold the osteoimplant duringimplantation and to easily place it at the proper location.

BRIEF DESCRIPTION OF THE SEVERAL VIEWS OF THE DRAWINGS

The FIGS. 1–6 represent different non-limiting examples ofosteoimplants.

FIGS. 1 and 2 illustrate a tapered osteoimplant made from a long bonediaphysis, e.g., femoral ring, shown generally as 10.

FIGS. 3 and 4 illustrate a tapered osteoimplant made from a segmenttaken from a partial ring shown generally as 100.

FIGS. 5 and 6 illustrate a cylindrical threaded dowel osteoimplant showngenerally as 200. Each of the above osteoimplants includes engagementstructure 12, 112, 212 for engaging an insertion tool to facilitateinsertion of the osteoimplant into an implant site.

FIGS. 7 and 8 illustrate various components that can be used tophysically mask portions of the osteoimplant during demineralizing.

FIGS. 9 and 10 illustrate the experimental method used to determine thehistomorphometry of bone used in the osteoimplant described herein.

FIG. 11 is a graph demonstrating the depth of demineralization of boneas a function of the time the bone is exposed to a demineralizingsolution.

FIGS. 12–18 illustrate the osteoinductivity of bone prepared asdescribed herein.

DETAILED DESCRIPTION OF THE INVENTION

The below definitions are intended to be understood in the broadestsense unless otherwise specified and serve to provide a clear andconsistent understanding of the specification and claims, including thescope to be given such terms.

The term “configuring” as utilized herein refers to any method ofmechanically or chemically changing the spatial appearance orconformation of an osteoimplant without limitation as to the specificapparatus employed. Therefore, methods of configuring would include avariety of operations, for example, cutting, shaving, slicing, milling,grinding, drilling, molding, shaping, turning, chiseling, dissolving,etching, etc. Thus, any and all possible methods of configuring areenvisioned as being within the scope of the disclosure herein.

The expression “clinically significant” as utilized herein refers to theabsence of any undesirable reduction in strength likely to cause anegative outcome in a patient having an osteoimplant as described hereinplaced at an implant site. It is to be understood that some reduction instrength is to be expected in any portion of bone that is demineralized.However, such reduction of strength according to the method herein wouldbe expected to improve the biological response of a patient, forexample, by improving conformability of the osteoimplant to the implantsite. Such improved biological response will be discussed in greaterdetail in a later section of this disclosure.

The term “osteoimplant” as utilized herein is intended to refer to anydevice or material for implantation that aids or augments bone formationor healing. Osteoimplants are often applied at a bone defect site, e.g.,one resulting from injury, defect brought about during the course ofsurgery, infection, malignancy or developmental malformation. Therefore,such “osteoimplants” are envisioned as being suitably sized and shapedas required for use in a wide variety of orthopedic, neurosurgical, andoral and maxillofacial surgical procedures such as the repair of simpleand compound fractures and non-unions, external and internal fixations,joint reconstructions such as arthrodesis, general arthroplasty, deficitfilling, discectomy, laminectomy, anterior cervical and thoracicoperations, spinal fusions, etc. Therefore, the osteoimplants utilizedherein are intended for implantation at a bony site and are made of anysubstantially monolithic bone and may be designed for either animal orhuman use. Specifically, the osteoimplant suitable for use according tothe disclosure herein will be any osteoimplant substantially fabricatedfrom a monolithic section of bone.

The expression “monolithic bone” as utilized herein refers to relativelylarge pieces of human or animal bone, i.e., pieces of bone, autograft,allograft, xenogenic, or transgenic, that are of such size andcomposition as to be capable of withstanding the sort of mechanicalloads to which functioning bone is characteristically subjected, e.g.,cortical bone. It is further to be understood that the expression“monolithic bone” refers to fully mineralized bone, i.e., bone with itsfull natural level of mineral content, and to such bone that has beendemineralized to some minor extent, i.e., to an extent which reduces theoriginal mechanical strength of the bone by no more than about 50percent. The monolithic bone can be provided as a single integral pieceof bone, preferably corticocancellous bone, more preferably corticalbone or as a piece of bone permanently assembled from a number ofsmaller bone elements such as, for example, composite bone and/orassembled bone as described in U.S. Pat. Nos. 5,899,939, 6,025,538,6,123,731, 6,200,347, the contents of each being incorporated herein byreference. Although monolithic bone can contain factors that areosteogenic, monolithic bone can also contain additional materials, e.g.,as disclosed in U.S. Pat. No. 5,290,558 the contents of which areincorporated herein by reference, which will remain with the bone afterits rehydration and will be present at the time of implantation.Monolithic bone can therefore include autograft, allograft, xenogenic,and transgenic material as well as mixtures thereof. Because bone itselfcontains small pores or channels, the monolithic bone useful herein canlikewise contain pores or channels whether naturally occurring or formedby mechanical means, e.g., drilling, laser machining, etc.

The term “load-bearing” as utilized herein shall be understood asmeaning capable of supporting a force as is typically applied at animplant site. The osteoimplant described herein will be considered to beload-bearing even if portions of the implant, e.g., demineralizedregions, are deformed by the force applied at an implant site. Of courseit will be understood by those skilled in the art that all materials arepotentially deformable by forces. However, the magnitude of deformationas a result of the same force being exerted upon a mineralized anddemineralized bone would differ greatly and might not be easilymeasurable in the mineralized bone.

The expression “engaging regions” and expressions of like import will beunderstood as referring to those regions of the osteoimplant that aresubstantially mineralized, either by masking before demineralizingand/or configuring a demineralized region to expose a mineralizedportion beneath, and are intended to reversibly connect with theattachment portion of an insertion tool or remain in sustained contactwith another implant or implant device at the surgical site.

The term “biocompatible” and expressions of like import shall beunderstood to mean the absence of stimulation of an unacceptablebiological response to an implant and is distinguished from a mild,transient inflammation and/or granulation response which can accompanyimplantation of most foreign objects into a living organism and is alsoassociated with the normal healing response. Materials useful to theinvention herein shall be biocompatible if, at the time of implantation,they are present in a sufficiently small concentration such that theabove-defined condition is achieved.

The term “autograft” as utilized herein refers to tissue that isextracted from the intended recipient of the implant. Such material willbe considered to be autograft even when prepared in tissue culture.

The term “allograft” as utilized herein refers to tissue intended forimplantation that is taken from a different member of the same speciesas the intended recipient.

The term “xenogenic” as utilized herein refers to material intended forimplantation obtained from a donor source of a different species thanthe intended recipient. For example, when the implant is intended foruse in an animal such as a horse (equine), xenogenic tissue of, e.g.,bovine, porcine, caprine, etc., origin may be suitable.

The term “transgenic” as utilized herein refers to tissue intended forimplantation that is obtained from an organism that has been geneticallymodified to contain within its genome certain genetic sequences obtainedfrom the genome of a different species.

The term “whole” as utilized herein refers to bone that contains itsfull mineral content.

The term “demineralized” as utilized herein refers to bone containingless than about 95% of its original mineral content.

The expression “fully demineralized” as utilized herein refers to bonecontaining less than about 5% of its original mineral content.

The term “acid” as utilized herein is intended to refer to any acid ormixture of acids capable of demineralizing bone, preferably hydrochloricacid. Other suitable acids include formic acid, acetic acid, peraceticacid, citric acid, propionic acid, other organic acids, etc. Suitableinorganic acids include the mineral acids hydrochloric acid, phosphoricacid, etc. Chelators such as ethylenediaminetetraacetic acid (EDTA) (oranalogues of this chelator such as EGTA), citric acid, succinic acid,heparin, etc. can be used to chelate (bind) calcium which aids in thedemineralization of bone by both organic and inorganic acids. Suitableranges of acid concentration would vary depending upon the strength ofthe acid (its ability to disassociate the mineral salts found in bone)and the temperature of the demineralizing solution and would range fromabout 0.1 molar to about 10 molar.

The term “osteogenic” as utilized herein shall be understood asreferring to the ability of an osteoimplant to enhance or accelerate thegrowth of new bone tissue by one or more mechanisms such asosteogenesis, osteoconduction and/or osteoinduction.

The term “osteoinductive” as utilized herein shall be understood torefer to the ability of a substance to recruit cells from the host thathave the potential for forming new bone and repairing bone tissue. Mostosteoinductive materials can stimulate the formation of ectopic bone insoft tissue.

The term “osteoconductive” as utilized herein shall be understood torefer to the ability of a non-osteoinductive substance to serve as asuitable template or substrate along which bone may grow.

Bone is the hard form of connective tissue that constitutes the majorityof the skeleton of most vertebrates. It consists of an organic component(the cells and matrix) and an inorganic, or mineral, component. Inprocessing bone intended for implantation, the cellular component isfrequently removed to reduce the antigenicity of the implant. The matrixcontains a framework of collagenous fibers and non-collangenous proteinsand is impregnated with the mineral component which imparts the qualityof rigidity to the bone.

The mineralized component of the bone is largely contained within thecortical region of the bone. This region of the bone contains freelyanastomosing channels that, in the native state, contain blood vessels,lymph vessels, and nerves. These channels are frequently referred to asHaversian canals.

As stated above, during preparation of bone intended for implantation,the cells are frequently removed. The removal of cells also results inthe removal of tissues generally associated with the bone such as, forexample, blood vessels, lymph vessels, nerves, etc. The initialprocessing of bone intended for implantation is known and described inU.S. Pat. Nos. 5,333,626, 5,513,662, and 5,846,484, the contents of eachbeing incorporated herein by reference. The removal of these tissuesresults in the formation of substantially empty Haversian canals. Thisportion of the cortical bone, consisting of a Haversian canal and itsconcentrically arranged lamellae, is referred to as an osteon. Theosteons are directed mainly in the long axis of the bone and aretypically about 200 μm in diameter.

It has been discovered herein that surface demineralization of anosteoimplant to a depth just sufficient to expose the osteons providesan osteoimplant having the desirable combined characteristics ofimproved biological response of the osteoimplant while maintaining amineralized core portion of the osteoimplant capable of sustainingmechanical loads such as those frequently encountered at an implantsite. Although not entirely understood, it is believed that theimprovement in the biological response is due to providing access to theHaversian system to allow cells such as, for example, osteoblasts,access to the mineralized core region of the osteoimplant. In addition,new chondrocytes can penetrate into demineralized Haversian canals ofthe demineralized region of the osteoimplant. It is believed that inthis manner the Haversian system serves as the “seed” ofosteoinductivity, thus allowing the implant to remodel from the insideout as well as the outside in. Of course, when desirable, small pores orcanals can be mechanically introduced into the osteoimplant. Forexample, when the osteoimplant is an aggregate or composite structure, avariety of materials and methods can be used to introduce the pores orcanals into the osteoimplant, e.g., small drill bits, a laser ofsuitable power and wavelength, water-jet cutters, hole-saws, etc. can beused to create appropriately dimensioned and configured passageways intothe interior regions of the osteoimplant. Such passageways willtypically have diameters between about 50 μm and about 1000 μm. Ofcourse, larger holes in the millimeter size range might also be usefulto assist with penetration of the osteoimplant with blood vessels, oneof the early stages of bone incorporation.

The demineralized zone of the surface of the osteoimplant of thisinvention is osteoinductive, and therefore promotes rapid new ingrowthof native host bone tissue into the osteoimplant. The demineralized zoneof the surface of the osteoimplant can be any surface portion. Forexample, when the osteoimplant is a femoral ring intended forimplantation as a spinal fusion device, the demineralized zone of thesurface can be limited to those surfaces intended to contact vertebra.When the osteoimplant is intended for a different application; e.g.,intercalary grafting, where the cut surface of the graft mates with thatof a long bone; onlay grafting, where the outer (endosteal, periosteal)or cut surface would be adjacent the periosteal surface of a bone; theadjacent portion of the osteoimplant can be the demineralized zone ofthe surface. In this manner the biological properties of theosteoimplant in relation to the graft receiving surface(s) can beimproved.

When it is desirable to provide an osteoimplant having improvedbiological properties while still substantially maintaining the strengthpresent in the osteoimplant prior to demineralization, the extent andregions of demineralization of the implant will be controlled. Forexample, the depth of demineralization must be at least about 100microns but depths of demineralization ranging up to about 7000 micronsor more may be entirely suitable depending on the intended applicationand graft site. Typically the depth of demineralization will be between100 to about 5000 microns, preferably from about 150 to about 2000microns, more preferably between about 200 microns to about 1000microns. Any and all such variations and combinations of demineralizedzone(s) of the surface of the osteoimplant as described above aretherefore envisioned as being within the scope of the disclosure herein.

Another significant advantage of the demineralized zone(s) is theability of demineralized bone to elastically yield under applied force.Thus, when the osteoimplant is subjected to an applied load at the siteof implantation, the demineralized zones on the surface of theosteoimplant can conform to the contours of adjacent bone tissue andthereby minimize voids or spaces between the osteoimplant and adjacentbone tissue. This is important because host bone tissue will not grow tobridge large voids or spaces. Thus, by conforming to the contours ofadjacent bone tissue, the osteoimplant of this invention exhibitsenhanced biological properties such as, for example, incorporation andremodeling. The non-demineralized inner core of the osteoimplant impartsmechanical strength and allows the osteoimplant to bear loads in vivo.Other non-demineralized zones provide improved tolerances when engagedwith other objects such as, for example, insertion instruments, otherimplants or implant devices, etc. This improved tolerance provides formore accurate insertion and/or retention of the osteoimplant at theimplant site than was provided by implants prepared according to theprior art. For example, the demands presented by endoscopic surgery ofthe anterior spine require an implant that can be precisely andreversibly engaged with endoscopic instrumentation. Therefore, anosteoimplant manufactured to maintain close tolerances in the instrumentengaging regions of the osteoimplant would be advantageous to surgeonswho typically employ such devices and methods.

In a preferred form, an osteoimplant is made available to surgeons in akit prepackaged with a delivery tool comprising means for holding theosteoimplant and then controllably releasing the osteoimplant. Thedelivery tool preferably includes releasable engaging means such as, forexample, thread end, friction fit, multiple engagement rods, a base anda pair of flexible opposed arms extending from the base, etc. Theengaging means is spaced and dimensioned to releasably hold the implant.A delivery tool handle is also provided so that the tool can be easilymanipulated by the surgeon.

In the preferred kit form, the delivery tool is made of a suitablematerial, e.g., stainless steel, titanium alloy, sterilizable plastic,etc. The kit is provided with the osteoimplant engaged with the deliverytool, in a presterilized package. The handle of the delivery tool mayalso be in the package integral with the delivery tool, or may beprovided separately. The osteoimplants are provided in a range of sizesfor different size persons and different locations of the disk to bereplaced. The surgeon makes a preoperative estimation of the range ofsizes most likely to be required, and delivery tool/osteoimplant setsspanning this range are prepared for surgery. During the implantprocedure, the surgeon can select the one osteoimplant that is mostappropriate, and substitute another if for some reason, typicallyincorrect dimensions, the first choice is not operable. The surgeon neednot modify the shape of the osteoimplant, but uses it directly from thepackage. The osteoimplant is placed into the correct position using thedelivery tool, the osteoimplant is controllably released, and thedelivery tool is removed and discarded. This approach minimizes the timeof the operation, thereby decreasing the chances of complications forthe patient.

As set forth above, the bone employed in the practice of the disclosureherein can be obtained from bone which, with respect to the finalimplant recipient, may be of autogenous, allogenic, xenogenic and/ortransgenic origin or mixtures thereof. Porcine and bovine bones areparticularly advantageous types of xenogenic bone tissue that can beused individually or in combination as sources for the bone although ofcourse other xenogenic or transgenic bone tissues can also be used.

The monolithic section of bone preferably includes the diaphysis ormetaphysis of a long bone, i.e., femur, tibia, fibula, humerus, ulna,radius; phalanges or smaller pieces, etc. obtained, for example, bymaking a transverse or longitudinal cut through the diaphysis ormetaphysis of a long bone. Such bone sections will typically possess atotal surface area of between about 100 mm² and about 10,000 mm²,preferably between about 250 mm² and about 8000 mm², more preferablybetween about 300 mm² and about 7600 mm². After the bone is obtainedfrom the donor and before it is subjected to a demineralizing step, itis processed, i.e., cleaned, disinfected, and defatted, etc., usingmethods that are conventional and well known in the art.

Methods for demineralizing the surface area of the monolithic section ofbone are known. Demineralization procedures remove the inorganic mineralcomponent of bone by employing acid solutions. Such procedures are wellknown in the art, see for example, Reddi et al., Proceeding of theNational Academy of Sciences of the United States of America 69, pp.1601–1605 (1972), incorporated herein by reference. The strength of theacid solution, the shape and size of the bone and the duration of thedemineralization procedure will determine the extent ofdemineralization. Control of these variables to effect the desiredextent of demineralization is well within the purview of those skilledin the art. Reference in this regard may be made to Lewandrowski et al.,Journal of Biomedical Materials Research, 31, pp. 365–372 (1996).

In a preferred demineralization procedure, the osteoimplant is subjectedto an acid demineralization step followed by a defatting/disinfectingstep. The osteoimplant is immersed in acid over time to effectdemineralization. Acids that can be employed in this step includeinorganic acids such as hydrochloric acid and as well as organic acidssuch as formic acid, acetic acid, peracetic acid, citric acid, propionicacid, etc. The depth of demineralization into the bone surface can becontrolled by adjusting the treatment time, temperature of thedemineralizing solution, concentration of the demineralizing solution,and agitation intensity during treatment.

The demineralized osteoimplant is rinsed with sterile water and/orbuffered solution(s) to remove residual amounts of acid and therebyraise the pH. A preferred defatting/disinfectant solution is an aqueoussolution of ethanol, the ethanol being a good solvent for lipids and thewater being a good hydrophilic carrier to enable the solution topenetrate more deeply into the bone particles. The aqueous ethanolsolution also disinfects the bone by killing vegetative microorganismsand viruses. Ordinarily, at least about 10 to 40 percent by weight ofwater (i.e., about 60 to 90 weight percent of defatting agent such asalcohol) should be present in the defatting disinfecting solution toproduce optimal lipid removal and disinfection within the shortestperiod of time. The preferred concentration range of the defattingsolution is from about 60 to about 85 weight percent alcohol and mostpreferably about 70 weight percent alcohol. In accordance with thisinvention, demineralization is conducted to a depth of from about 100 toabout 7000 microns, preferably from about 150 to about 2000 microns, andmore preferably from about 200 to about 1000 microns.

In addition to the demineralizing step, the monolithic section of boneis optionally subjected to a configuring step to form the osteoimplantdescribed herein. The configuring step can be employed usingconventional equipment to produce a wide variety of geometries, e.g.,threaded holes, at least two receiving holes, concave or convexsurfaces, stepped surfaces, cylindrical dowels, cortical rings, wedges,blocks, screws, pins, and the like. The configuring step can also beemployed to provide a vertebral interbody fusion device configured tospan an intervertebral space between adjacent vertebrae.

The configuring step can be performed before and/or after thedemineralizing step depending upon the intended end use of theosteoimplant and any specific properties to be imparted to the implant.It is contemplated that the configuring step, when performed after thedemineralizing step, can result in the removal of some but not all ofthe demineralized zone(s) on the outer surface of the osteoimplant, thusselectively exposing non-demineralized bone on the outer surface of theosteoimplant. Thus, the outer surface of the osteoimplant can beprovided with zones of demineralized bone as well as non-demineralizedbone. These zones can be selected based on the geometry and function ofthe implant. For example, those surface areas of the osteoimplant thatwill come in direct contact with adjacent host bone tissue can beprovided with demineralized zones to promote fusion with adjacent hostbone tissue, whereas those surface areas that will require mechanicalstrength, e.g., threaded holes adapted to receive screws or surfacesadapted to mate with metallic implants, can be provided withnon-demineralized zones.

When the osteoimplant is configured prior to demineralization, specificareas, cavities, holes, etc., of the osteoimplant can be treated tolimit the extent of demineralization of such treated regions. Forexample, the treatment can consist of any suitable barrier to preventcontact of the mineralized region with the demineralizing solution.Therefore, such treatment can include “masking” agents or chemicalcoatings, e.g., Epon™, paraffin wax, petroleum jelly, polymericmaterials that are solidifiable and substantially removable, coveringthe surface to remain mineralized with a dissolvable material, forexample, calcium phosphate, calcium sulfate, calcium carbonate,magnesium whitlockite, Bioglass, etc. which is preferably removed priorto implantation, covering the surface to remain mineralized with asufficient amount of a material more reactive with the demineralizingsolution than bone and also doesn't dissolve readily in water and/ortreatments to increase the hydrophobicity of a specific portion of theimplant as well as the use of a physical barrier to occupy the cavity,hole, etc., that is desired to be maintained in a mineralized condition.For example, a threaded hole can be provided in an osteoimplant prior todemineralization. When a component such as, for example, a mating screw,a rubber or polymeric plug, etc., that is non-soluble and non-reactivewith the demineralizing solution, e.g., surgical stainless steel,plastic, ceramic, etc., is screwed or inserted into the mating hole suchthat the region is occupied prior to demineralizing the osteoimplant,the component will prevent contact of the occupied region of theosteoimplant with the demineralizing solution and that region willtherefore remain substantially mineralized and will not experience anysignificant change in its dimensions. An advantage of this approach topreventing undesirable demineralization as compared to coating ortreating the region of the osteoimplant to remain mineralized is theease in covering the desired area prior to demineralization, and theease in “unmasking” the area after demineralization. Alternatively, thecutting or machining bit itself can be the masking agent if left inplace in the implant during the demineralization process. Additionally,when using mechanical fasteners, the fasteners themselves can be used inthe demineralization process as fixtures by which the osteoimplant issuspended in the demineralizing solution.

When the osteoimplant is configured after surface demineralization,certain advantages can be observed. For example, because any dimensionalchange due to demineralizing has already occurred, configuring theosteoimplant after demineralizing provides an osteoimplant which mateswell with surgical instruments and other mechanical devices. This wouldbe especially advantageous in applications where there is a need for theosteoimplant to hold tighter tolerances, e.g., a region of rigidity tohold screw threads, friction fitting the implant on an inserter thatuses a press-fit attachment scheme, etc. Thus an osteoimplant that isconfigured after demineralizing would demonstrate improved retention ofshape compared to an unmasked osteoimplant that is configured prior todemineralizing. In addition, configuring the osteoimplant afterdemineralizing would be beneficial in applications requiringincorporation of the implant faster in certain areas of the implant thanin others.

In certain embodiments, the osteoimplant is coated and/or treated asdescribed above to provide certain zones that remain substantiallymineralized even after the osteoimplant has been exposed todemineralizing treatment. These embodiments may provide osteoimplantsthat are suitable for use as disclosed herein that are more easilyprepared, e.g., fewer process steps, than osteoimplants requiring aconfiguring step to form the general shape of the implant, ademineralizing step to provide desirable biological characteristics tothe implant, and a subsequent configuring step to provide desirablemineralized portions of the osteoimplant. Of course, depending upon theintended use of an osteoimplant as described herein, any suitablecombination of coating and/or configuring, either before or after thestep of demineralizing, may be useful according to the disclosureherein.

In a preferred embodiment, the monolithic section of bone is obtained bymaking a transverse cut through the diaphysis or metaphysis of aprocessed long bone to obtain a cylindrical portion possessing a totalsurface area typically ranging from about 300 to about 7500 mm²,demineralizing part or all of the outer surface of the cylindricalportion to a depth of from about 100 to about 1000 microns, andconfiguring the surface demineralized cylindrical portion to provide anintervertebral implant. If desired, the outer surface of theintervertebral implant can be masked with an acid resistant coating orotherwise treated as described above to selectively demineralizeunmasked portions of the outer surface of the intervertebral implant.

Exemplary intervertebral implants which can be fabricated by configuringthe surface demineralized cylindrical portion are disclosed in U.S.patent application Ser. No. 09/328,242 entitled Ring-ShapedIntervertebral Implant, U.S. patent application Ser. No. 09/327,982entitled Keyed Intervertebral Dowel and U.S. patent application Ser. No.09/328,283 entitled Intervertebral Implant. Each of these applicationsis incorporated herein by reference. Other exemplary assembled and/orcomposite implants would include U.S. Pat. Nos. 5,728,159, 5,895,426,6,025,538, and 6,200,347. Each of these patents is incorporated hereinby reference.

Preferred embodiments of the presently disclosed method for preparing apartially demineralized bone graft will now be described in detail withreference to the drawings (FIGS. 1–6) in which like reference numeralsdesignate identical or corresponding elements in each of the severalviews. In the presently disclosed method for preparing a partiallydemineralized osteoimplant, the engagement structure 12, 112, 212, whichin each of these implants includes, for example, a threaded bore, isfilled with a physical barrier (e.g., a plug) prior to immersing theosteoimplant in acid. As previously stated, in order to preventdemineralization from occurring, the plug is preferably formed of amaterial that is non-soluble and non-reactive in the demineralizingagent. Such materials may include plastics, metals, ceramics,composites, etc. Alternately, the plug may be formed of a materialhaving a pre-selected dissolution rate or activity in acid such that alimited degree of demineralization is permitted to occur adjacent to theportion of the osteoimplant that has been plugged. In yet a furtherembodiment, the plug can be shaped and configured in a manner to assistin the demineralization process. For example, the plug can be perforatedto allow access of the demineralization solution to certain regions ofthe bone. Alternatively, the plug can be configured to serve as aninterface for such a pressure-flow system as described in U.S. Pat. No.5,846,484.

The plug preferably has a shape that corresponds to the shape of therecess defining the engagement structure 12, 112, 212, of the bonegraft. For example, the plug 50 may be in the form of a threaded screw(FIG. 7). Alternately, plug 50 may be frictionally retained within theengagement structure. Referring to FIG. 8, plug 50 may include a head 52for masking the bone adjacent the engagement structure or recess that isbeing plugged.

The invention will be better understood by way of the following exampleswhich are intended to illustrate but not limit the invention in anywaywhatsoever.

EXAMPLE 1

Surface Demineraliztion

A study was undertaken to determine the effect of varying penetration ofsurface demineralization on the osteoinductive response to humancortical bone implants using an athymic rat intramuscular assay.Osteoinductivity is often defined as the ability of the agent to recruitcells to the site, and to convert them to the osteoblastic lineage.Osteoinductivity has been observed to follow an “endochondral pathway”similar to that of embryonic bone when it is first formed. This bonegoes though stages, including the penetration and infiltration of cellsinduction of chondrogenic (cartilage-forming) cells at the site, layingdown of cartilage tissue, and the transformation of that cartilagetissue to bone tissue. All of these changes can be tracked over time inhistological samples.

Implants were constructed aseptically from human cortical bone.Cylindrical discs (7±1 mm in diameter and 3±0.5 mm thick) were cut fromcortical bone of the same donor. Before demineralization and aftercutting, the bone discs were washed in water for injection (WFI),sonicated in 70% ethanol for one hour, and washed again with WFI. Thediscs were surface demineralized in 0.6N HCl solution at six differenttime points in order to vary the demineralization layer thicknesses.

Demineralization time points were A=0 hr. B=0.25 hr, C=0.5 hr, D=1 hr,E=2 hr, and F=4 hr. Ten discs were prepared in each of the 6 treatmentgroups. Two discs from each treatment group were reserved for initialX-rays (FIG. 12) and histomorphometry of demineralization penetration(FIGS. 13–18).

An athymic rat model was used to evaluate osteoinduction in thisinvestigation. Standard surgical intramuscular implantation of the discswas performed on 24 rats with two implants, randomly chosen. Discs wereoriented in the same manner within the musculature. Animals weresacrificed at 28 days. Each treatment group contained eight samples.

One disc from each time point was X-rayed with a Faxitron (HewlettPackard) for 54 seconds at 50 kv. Each explanted sample was also X-rayedfor 54 seconds at 50 kv.

One disc from each time point was placed in 3% basic fuchsin in order tostain the demineralized surface. Discs were cut in half down the centralaxis (FIG. 9), photographed, acquired with Adobe Photoshop 5.0, andanalyzed with Image-Pro Plus 3.1. The actual depth of demineralizationwas calculated by measuring the length (pixels) of the staineddemineralized area at several locations (D_(p) and D_(r)) for each timepoint. The pixel measurements were averaged and converted tomillimeters.

Specimens for histological analysis were harvested with attachedsurrounding host tissues intact to preserve the host-graft tissueinterface. Half the specimens were demineralized, dehydrated, and cut inhalf down the central axis. Both exposed surfaces were embedded inglycol methacrylate (JB-4) and oriented to allow simultaneous sectioningof each exposed surface. Four 5-μm sections were taken at 100 μmintervals for each sample. Sections were stained with toluidine blue.Sections were microscopically evaluated to determine osteoinductivesurface involvement, penetration, and overall osteoinductive response.

The remaining half was dehydrated and embedded in methyl methacrylate todifferentiate demineralized tissues. The cylindrical test article wassectioned as shown in FIG. 10, in 1 mm increments, mounted on opaqueplastic slides and hand ground when necessary.

The estimated (based upon Lewandrowski's equation for planardemineralization) and actual demineralization depths for each treatmentgroup are listed below in Table 1.

TABLE 1 Demineralization Depth Treatment from Planar Surface (mm) Numberof Identification Treatment Estimated Actual (av.) discs A  0 minutes 00 10 B 15 minutes 0.182 0.104 10 C 30 minutes 0.257 0.218 10 D  1 hour0.364 0.419 10 E  2 hours 0.515 0.502 10 F  4 hours 0.728 0.657 10

The actual depths of demineralization plotted against the duration ofexposure to the acid shows that the rate of surface demineralizationbegins to slow after one hour (FIG. 11).

The fully demineralized histology clearly shows the areas of surfacedemineralization. A very fine fibrous tissue layer encapsulated thediscs. An inductive response, indicated by either chondrocytes or newbone formation, was evident in all of the partially demineralizedsamples. However, because of the fine encapsulation, this inductiveresponse was generally limited to Haversian canals in the demineralizedportion. Activity was also present in some of the canals in themineralized portion as long as some proportion of that canal wasdemineralized. Therefore, the greater the depth of demineralization, themore Haversian systems are exposed, and the greater the inductiveresponse (FIGS. 13–18).

EXAMPLE 2

Spinal Fusion Procedure

In this example, the insertion of osteoimplants having an engagementstructure (12, 112, 212) in conjunction with a posterior approach forlumbar discectomy and spinal fusion will be discussed. It is to beappreciated that other surgical approaches, e.g., anterior,postero-lateral, etc., may be utilized to perform the discectomy andinsert engagement structure as well.

Initially, the vertebral column is accessed via a posterior approachwith the use of appropriate retractors to retract neighboring muscletissue, blood vessels and/or nerve tissue. Thereafter, at least aportion of the disc is removed with an appropriate rongeur or cuttingimplements. A retractor is mounted to the posterior faces of thevertebrae. One retractor suitable for this purpose is the Cloward LumbarLamina Spreader manufactured by Codman. The retractor includes a pair ofretractor arms which are mountable to the posterior vertebral faces viascrews. With the retractor appropriately mounted, the arms of theretractor are spread to distract the adjacent vertebrae to provideadequate clearance for insertion of the osteoimplant having engagementstructure between the vertebrae. The osteoimplant having engagementstructure is thereafter inserted into the distracted space with anappropriate engaging instrumentation where it is received within theintervertebral space. Once the osteoimplant having engagement structureis appropriately positioned within the intervertebral space, theretractor is returned to return the adjacent vertebrae to their normalpositions.

The osteoimplant having engagement structure forms a strut supportingand maintaining the adjacent vertebrae in desired spaced relation. Inpractice, optimum dimensions for the osteoimplant having engagementstructure are determined, in part, by the dimensions of the spacebetween the adjacent vertebrae and by the desired space if the diskheight has been reduced by disease. The contact of the vertebralsurfaces with the conformable demineralized surfaces of the osteoimplanthaving engagement structure allows for relatively rapid osteoinductionand subsequent fusion. Over a period of time, the bone tissue fromadjacent vertebral bodies grow within and fuse with the osteoimplanthaving engagement structure to form a solid fusion.

As demonstrated in Example 1, surface demineralization elicits aninductive response on mineralized tissue. This response is proportionalto the depth of demineralization. A critical depth of about 100 μm toabout 200 μm has been observed to be required for initiation ofosteoinduction. The rate of demineralization is greatest within thefirst hour of exposure to the acid solution. The 0.25 hrdemineralization exposed very few Haversian canals and concurrently hadminimal evidence of osteoinduction. The 0.5 hr and 1 hr time pointsshowed a notable number of demineralized canals and therefore showedevidence of osteoinduction throughout the demineralized layer. The 2 hrand 4 hr time points do not show a noticeably greater amount ofosteoinduction than the previous two time points. Since additionaldemineralization will degrade the implant's mechanical properties, theoptimal duration of demineralization is between 0.5 hr. and 1 hr toachieve the combined biological and mechanical goals of the implant.

It will be understood that various modifications may be made to theembodiments disclosed herein. For example, the method described hereincan be used to mask any recess load-bearing (or non-load-bearing)surface on a bone graft. The method is not limited to masking bone graftengagement structure. Moreover, the plug need not be cylindrical inshape but rather can be formed to correspond to the shape of any recessformed in a bone graft. Therefore, the above description should not beconstrued as limiting, but merely as exemplifications of preferredembodiments. Those skilled in the art will envision other modificationswithin the scope and spirit of the claims appended hereto.

1. A surface demineralized osteoinductive osteoimplant comprising rigidmonolithic bone, the bone comprising at least one outer surfacedemineralized zone at least about 100 microns thick, the bone furthercomprising a non-demineralized core region, the non-demineralized coreregion being proximate to and beneath the at least one outer surfacedemineralized zone, wherein the non-demineralized core region is definedin at least two directions by the at least one outer surfacedemineralized zone.
 2. The osteoimplant of claim 1, wherein, the bone isselected from the group consisting of autogenic bone, allogenic bone,xenogenic bone, transgenic bone, composites thereof, and assembliesthereof.
 3. The osteoimplant of claim 1, wherein the outer surfacedemineralized zone is from about 100 to about 2000 microns thick.
 4. Theosteoimplant of claim 3, wherein the outer surface demineralized zone isfrom about 200 to about 1000 microns thick.
 5. The osteoimplant of claim1, wherein the outer surface demineralized zone comprises a thicknesssufficient to expose osteons and provide access to Haversian canalswithin the bone.
 6. The osteoimplant of claim 1, further comprisingpassageways extending from the outer surface towards thenon-demineralized core region, wherein each passageway has a diameter ofbetween about 50 and about 1000 microns.
 7. The osteoimplant of claim 1,wherein the bone further comprises at least one outer surfacenon-demineralized zone wherein the outer surface non-demineralized zonecomprises at least one engagement structure for reversible engagementwith an insertion device.
 8. The osteoimplant of claim 7, wherein theengagement structure has a shape selected from the group consisting ofthreaded holes, receiving holes, hex shaped recesses, concave surfaces,convex surfaces, stepped surfaces, tapered surfaces, flat surfaces,serrated surfaces, wedges, blocks, screws, pins, and combinationsthereof.
 9. The osteoimplant of claim 7, wherein the non-demineralizedzone is provided by masking a region of the bone defining thenon-demineralized zone prior to demineralization.
 10. The osteoimplantof claim 7, wherein, the non-demineralized zone is provided byconfiguring at least a portion of the demineralized zone to expose thenon-demineralized zone.
 11. A load-bearing vertebral interbody fusiondevice comprising a rigid monolithic section of bone configured to spana space selected from the group consisting of an intervertebral spacebetween adjacent vertebrae and a space between non-adjacent vertebrae,the bone comprising at least one outer surface demineralized zone forcontacting the adjacent vertebra, the bone further comprising anon-demineralized core region, the non-demineralized core region beingproximate to and beneath the at least one outer surface demineralizedzone, wherein the non-demineralized core region is defined in at leasttwo directions by the at least one outer surface demineralized zone. 12.The fusion device of claim 11, wherein the outer surface demineralizedzone comprises a thickness sufficient to expose osteons and provideaccess to Haversian canals within the bone.
 13. The fusion device ofclaim 11, further comprising passageways extending from the outersurface towards the non-demineralized core region, wherein eachpassageway has a diameter of between about 50 and about 1000 microns.14. The fusion device of claim 11, wherein the bone further comprises anouter surface non-demineralized zone wherein the outer surfacenon-demineralized zone comprises at least one engagement structure formaintaining relatively close tolerances with an insertion instrument.15. The fusion device of claim 14, wherein the engagement structure hasa shape selected from the group consisting of threaded holes, receivingholes, hex shaped recesses, concave surfaces, convex surfaces, steppedsurfaces, tapered surfaces, flat surfaces, serrated surfaces, wedges,blocks, screws, pins, and combinations thereof.
 16. The fusion device ofclaim 14, wherein the outer surface demineralized zone is at least about100 microns thick.
 17. The fusion device of claim 16, wherein the outersurface demineralized zone is from about 100 to about 2000 micronsthick.
 18. The fusion device of claim 17, wherein the outer surfacedemineralized zone is from about 200 to about 1000 microns thick.
 19. Aload-bearing osteoinductive osteoimplant comprising a rigid monolithicsection of bone, said bone comprising at least one outer surfacedemineralized zone, said bone further comprising a non-demineralizedcore region proximate to and beneath the at least one outer surfacedemineralized zone, wherein said non-demineralized core region isdefined in at least two directions by the at least one outer surfacedemineralized zone, and wherein the outer surface demineralized zone isfrom about 100 to about 2000 microns thick.
 20. The osteoimplant ofclaim 19, wherein the bone is selected from the group consisting ofautograft bone, allograft bone, xenogenic bone, transgenic bone,composites thereof, and assemblies thereof.
 21. The osteoimplant ofclaim 19, wherein the bone is obtained from a bone selected from thegroup consisting of diaphysis of a femur, diaphysis of a tibia,diaphysis of a fibula, diaphysis of a humerus, diaphysis of an ulna,diaphysis of a radius, metaphysis of a femur, metaphysis of a tibia,metaphysis of a fibula, metaphysis of an ulna, metaphysis of a radius,phalanges, composites thereof, and assemblies thereof.
 22. Theosteoimplant of claim 19, wherein the bone further comprises anengagement portion having at least one geometry selected from the groupconsisting of threaded holes, receiving holes, hex shaped recesses,concave surfaces, convex surfaces, stepped surfaces, cylindrical dowels,cortical rings, wedges, blocks, screws, and pins.
 23. The osteoimplantof claim 22, wherein the engagement portion is substantiallynon-demineralized.
 24. The osteoimplant of claim 19, wherein the outersurface demineralized zone is from about 200 to about 1000 micronsthick.
 25. The osteoimplant of claim 19, wherein the outer surfacedemineralized zone comprises a thickness sufficient to expose osteonsand provide access to Haversian canals within the bone.
 26. Theosteoimplant of claim 19, further comprising passageways extending fromthe outer surface towards the non-demineralized core region, whereineach passageway has a diameter of between about 50 and about 1000microns.
 27. A vertebral interbody fusion device comprising a monolithicsection of rigid bone configured to span an intervertebral spaceselected from the group consisting of an intervertebral space betweenadjacent vertebrae and a space between non-adjacent vertebrae, said bonecomprising at least one outer surface demineralized zone, said bonefurther comprising a non-demineralized core proximate to and beneath theat least one outer surface demineralized zone, wherein thenon-demineralized core is defined in at least two directions by the atleast one outer surface demineralized zone, and wherein the outersurface demineralized zone is from about 100 to about 2000 micronsthick.
 28. The fusion device of claim 27, wherein the bone is selectedfrom the group consisting of autograft bone, allograft bone, xenogenicbone, and transgenic bone.
 29. The fusion device of claim 27, whereinthe bone is obtained from a bone selected from the group consisting ofdiaphysis of a femur, diaphysis of a tibia, diaphysis of a fibula,diaphysis of a humerus, diaphysis of an ulna, diaphysis of a radius,metaphysis of a femur, metaphysis of a tibia, metaphysis of a fibula,metaphysis of an ulna, metaphysis of a radius, phalanges, compositesthereof, and assemblies thereof.
 30. The fusion device of claim 27,wherein the bone further comprises an engagement portion having at leastone geometry selected from the group consisting of threaded holes,receiving holes, hex shaped recesses, concave surfaces, convex surfaces,stepped surfaces, cylindrical dowels, cortical rings, wedges, blocks,screws, and pins.
 31. The fusion device of claim 30, wherein theengagement portion is substantially non-demineralized.
 32. The fusiondevice of claim 27, wherein the outer surface demineralized zone is fromabout 200 to about 1000 microns thick.
 33. The fusion device of claim27, wherein the outer surface demineralized zone comprises a thicknesssufficient to expose osteons and provide access to Haversian canalswithin the bone.
 34. The fusion device of claim 27, further comprisingpassageways extending from the outer surface towards thenon-demineralized core region, wherein each passageway has a diameter ofbetween about 50 and about 1000 microns.